Transcatheter coronary sinus mitral valve annuloplasty procedure and coronary artery and myocardial protection device

ABSTRACT

Devices and methods are disclosed for the treatment or repair of regurgitant cardiac valves, such as a mitral valve. An annuloplasty device can be placed in the coronary sinus to reshape the mitral valve and reduce mitral valve regurgitation. A protective device can be placed between the annuloplasty device and an underlying coronary artery to inhibit compression of the underlying coronary artery by the annuloplasty device in the coronary sinus. In addition, the protective device can inhibit compression of the coronary artery from inside the heart, such as from a prosthetic mitral valve that exerts radially outward pressure toward the coronary artery. The annuloplasty device can also create an artificial inner ridge or retaining feature projecting into the native mitral valve region to help secure a prosthetic mitral valve.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation-in-part of U.S. patent application Ser. No. 13/468,761, filed May 10, 2012, now U.S. Pat. No. 9,271,833, issued Mar. 1, 2016, which is a divisional of U.S. patent application Ser. No. 12/514,990, filed May 14, 2009, now U.S. Pat. No. 8,211,171, issued Jul. 3, 2012, which is the U.S. National Stage of PCT/US2007/023876, filed Nov. 13, 2007, and which claims the benefit of U.S. Provisional Application No. 60/858,716, filed Nov. 14, 2006, and U.S. Provisional Application No. 60/932,611, filed May 31, 2007, all of which are incorporated by reference herein in their entirety.

FIELD OF THE DISCLOSURE

The present disclosure relates to annuloplasty techniques and devices in which tensioning elements are placed in the coronary sinus to perform mitral valve annuloplasty and treat mitral valve regurgitation.

BACKGROUND

Mitral valve regurgitation is a common cardiac valve disorder that can be caused by a primary valvular problem (such as damaged valve leaflets) or functional problems that impair leaflet coaption. A common cause of functional mitral valve regurgitation is dilated cardiomyopathy caused by myocardial infarction, chronic myocardial ischemia, hypertension, myocarditis, or other causes of heart muscle injury. Enlargement of the mitral annulus and left ventricular cavity produce mitral valvular insufficiency that can cause volume overload that further exacerbates the underlying myopathy and worsens the valvular insufficiency. Mitral valve repair can reduce mitral regurgitation and correct secondary mitral annular dilation to thereby improve mitral valve leaflet coaption. One such repair technique is an annuloplasty procedure, in which the annulus of the valve is surgically reconstructed or augmented by placement of a ring around the valve annulus to reduce its circumferential and septal-lateral dimensions. In patients with congestive heart failure and secondary mitral regurgitation, annuloplasty can provide a long-term symptomatic and survival benefit

Traditional mitral valve annuloplasty requires open heart surgery with a sternotomy or thoracotomy and cardiac arrest and cardio-pulmonary bypass. For example, the annuloplasty procedure is performed through a surgical incision in which the effective size of the valve annulus is reduced by attaching a prosthetic annuloplasty ring to the left atrial aspect of the mitral valve annulus. A variety of rigid and flexible annuloplasty rings have been developed for this purpose, such as those shown in U.S. Pat. Nos. 4,917,698; 5,041,130; 5,061,277; 5,064,431; 5,104,407; 5,201,880; and 5,350,420. Although very effective, this open-heart procedure is accompanied by substantial morbidity and prolonged convalescence. As a result, the procedure often is not offered to patients who are insufficiently symptomatic to justify the surgical risk and morbidity, or to patients who suffer advanced disease, or to patients with substantial co-morbidity.

Percutaneous approaches to mitral valve repair have been developed to reduce the clinical disadvantages of the open-heart procedures. In some percutaneous technique, a prosthesis is advanced in a catheter through the subject's vasculature to the vicinity of the mitral valve. These percutaneous techniques are attractive alternatives to conventional surgical treatment because they do not require open heart surgery or extracorporeal circulation, and can be used in a closed and beating heart. The treatment is potentially less morbid and can be applied to a wider range of patients including those with less severe valvular dysfunction.

Examples of percutaneous mitral valve repair procedures include coronary-sinus shortening devices, transcameral fixtures, endoventricular annular plication, and direct leaflet stapling. Coronary sinus annuloplasty techniques have been disclosed, for example, in U.S. Pat. Nos. 6,402,781 and 7,090,695 as well as U.S. Patent Publication Nos. 2004/0254600; 2005/0027351; and 2007/0073391. Some trans-sinus approaches aim to improve mitral valve coaptation by introducing a prosthesis into the coronary sinus to exert forces that reduce the circumference of the posterior mitral annulus or move the posterior annulus toward the anterior leaflet. Coronary sinus methods take advantage of the proximity of the coronary sinus to the mitral valve annulus, such that the pressure of the prosthesis in the coronary sinus pushes the fibrous annulus or the nearby atrial wall inward to reduce the diameter of the annulus.

However, these techniques have shown only limited success in establishing circumferential tension that characterizes effective surgical ring annuloplasty. The sinus-shortening devices have induced only local shortening across the mitral commissures but do not adequately reduce the septal-lateral separation that characterizes functional mitral valve regurgitation. The leaflet procedures have not been able to reduce annular dilation and they can also impair the normal dynamic line of mitral valve coaption that accommodates a range of volumes and inotropic states.

A more recent improvement of percutaneous annuloplasty is coronary sinus transcatheter-mitral-valve cerclage annuloplasty in which a tensioning material is placed around the mitral valve annulus using a catheter, such as a steerable guide wire or canalization catheter. Certain cerclage trajectories can compensate for coronary sinus anatomy that is remote from the mitral valve annulus, by rotating the plane of circumferential tension toward the left ventricular outflow tract. In cerclage, a continuous strand of tensioning material (such as suture material) is applied along a pathway that extends at least partially through the coronary sinus and then reenters the right side of the heart, for example by passing through a basal septal perforator vein and penetrating a small distance through septal myocardium. The tensioning material is placed with the assistance of imaging technologies that may include X-ray fluoroscopy, magnetic resonance imaging, intracavitary or external ultrasound, electroanatomic mapping, X-ray computed tomography or a combination (fusion) of any of these imaging technologies.

SUMMARY OF THE DISCLOSURE

Trans-sinus approaches that use the cerclage technique or other indwelling coronary sinus prostheses can have limiting drawbacks, however, because the coronary sinus and its branches have now been found to cross the outer diameter of major coronary arteries in a majority of humans. As a result, pressure applied by any prosthetic device in the coronary sinus (such as tension on the annuloplasty device) can compress the underlying coronary artery and induce myocardial ischemia or infarction. In particular, the coronary sinus usually extends superficial to the circumflex coronary artery and its marginal branches near the great cardiac vein, and trans-sinus annuloplasty transmits pressure sufficient to constrict or occlude the underlying coronary artery. Whether coronary obstruction occurs during coronary sinus annuloplasty depends on the spatial relationship between the coronary artery and vein. In a majority of humans, the coronary vein crosses over the left circumflex artery, which has limited the usefulness of coronary sinus annuloplasty. Given the foregoing, there is a need for methods that avoid constricting coronary artery branches during trans-sinus annuloplasty.

Devices and methods are described herein for protecting underlying myocardial structures such as myocardial tissue or coronary artery branches from constriction during trans-sinus mitral annuloplasty. The device can protect a coronary vessel from compression during mitral annuloplasty in which an annuloplasty element, such as a tensioning device, extends at least partially through the coronary sinus over a coronary artery. The device is a surgically sterile bridge configured for placement within the coronary sinus at a location where the coronary sinus passes over a coronary artery, so that the protection device provides a support for a mitral annuloplasty element, such as a compressive prosthesis, including a tension element when it is placed under tension. The protection device has an arch of sufficient rigidity and dimensions to support the tensioning element over the coronary artery, redistribute tension away from an underlying coronary artery, and inhibit application of pressure to the underlying artery, for example when an annuloplasty tension element is placed under tension during mitral annuloplasty.

In particular embodiments, the protective device is a support interposed in the coronary sinus between the annuloplasty device and the coronary artery. In one disclosed example, the protective device has guides on it that retain the annuloplasty device on the support. Such a guide can take the form of an internal lumen that extends the length of the support and through which a mitral annuloplasty tension element can extend so that the protective device supports the tension element away from the coronary artery. The device may be substantially tubular so that the tensioning element is contained within the protective device and supported in spaced relationship to the coronary artery. The arch may be configured to extend between a proximal foot and a distal foot that are substantially collinear with one another so that the feet form stabilizing members that retain the bridge in position over the coronary artery.

In particularly advantageous examples, the central arch bridges a linear distance at its base of from about 0.5 inches to about 0.6 inches, for example about 0.52 inches to about 0.55 inches, such as about 0.536 inches. In disclosed examples the central arch is from about 0.15 inches to about 0.16 inches high, for example about 0.1545 inches high, and the bridge has an outer diameter that is from about 0.04 to about 0.05 inches (for example 0.045 inches) along its entire length, and an inner diameter that is from about 0.025 inches to about 0.035 inches (for example 0.030 inches) along its entire length. In other examples, the protective device is made of a shape memory material, such as nitinol.

The device may be used in methods of improving the function of a mitral valve in a subject in which an annuloplasty element, for example an element that exerts compressive remodeling forces on the mitral valve (such as a tensioning element), is introduced at least partially around the mitral valve, for example at least partially through the coronary sinus and over a coronary artery. The protective device is placed between the annuloplasty element and the coronary artery, with the annuloplasty element separated from the underlying coronary artery by the bridge of the device. Compressive remodeling forces are exerted by the annuloplasty device (for example by applying tension on a tensioning element to alter the shape or configuration of the mitral valve annulus to reduce its circumference) while supporting the annuloplasty element on the bridge to inhibit application of pressure to the coronary artery. The function of the mitral valve in the patient is thereby improved without impairing coronary blood flow.

In some embodiments, the annuloplasty element is introduced at least partially around the mitral valve by advancing the annuloplasty element in an endovascular catheter through the vascular system of the subject to the heart, and introducing the annuloplasty element and the protective device from the catheter into the coronary sinus through a coronary sinus ostium. The annuloplasty element may, for example be a tensioning element such as a ligature, which in some embodiments is suture material. In those embodiments in which the protective device includes an internal lumen, the annuloplasty element extends through the lumen of the protective device over the coronary artery so that the annuloplasty element is supported by the protective device. The protective device can be integrated directly into the annuloplasty element, such as a resilient or expandable device, or a tensioning element or tensioning material.

In other embodiments, this disclosure provides a method of improving function of a mitral valve in a subject who has mitral regurgitation by performing a mitral valve cerclage annuloplasty. In a particular disclosed example of the procedure, a guiding catheter is percutaneously inserted through the vasculature of a subject. The guiding catheter is introduced through the coronary sinus and over an underlying coronary artery or other heart structure that is to be protected with the device. In one example, the catheter is introduced into the great cardiac vein, and a steerable microcatheter or other coaxial guiding catheter or steering device introduces a guidewire or other penetrating device (such as a needle, radiofrequency energy ablation device or laser ablation device) into a basal blood vessel such as the first septal coronary vein. From there the penetrating device directly traverses under imaging guidance the septal myocardium or annulus fibrosis and reenters the right ventricle or right atrium.

The guidewire is then retrieved using, for example, a vascular snare, and the guiding catheter and guidewire are replaced with a tensioning system. The protective device is then introduced through the guiding catheter over or in tandem with the tensioning system so as to protect an underlying coronary artery when tension is introduced to perform the annuloplasty. The location of the jeopardized coronary artery is identified, for example, by radiocontrast angiography or by fusion of prior computed tomography angiography and live X-ray or using intravascular ultrasound. In an alternative approach, coronary veins are entered in the other direction from the right atrium or right ventricle under imaging guidance into a branch of the coronary sinus.

Tension is applied through, for example, suture material exchanged for the cerclage guidewire. Tension can be applied through both ends of the suture as they are externalized at the point of vascular access. Tension is applied under imaging guidance until the desired degree of mitral annular circumferential reduction is accomplished, or until the mitral valve regurgitation is reduced, or until other deleterious endpoints are achieved such as mitral valve inflow obstruction. Tension is secured using a tension fixation device applied to both ends of the suture at the right atrium or right ventricle where the two cerclage trajectories cross, or at the point of vascular access, or in between the two. Tension is delivered by counterpressure against the fixation device, for example, applied through a delivery catheter. Before fixation, tension can be released or reduced, for example, to reposition the protection device or to achieve a lower degree of mitral annular circumferential reduction.

In some embodiments, the protection device can be incorporated during manufacture into the tension suture device, such that longitudinal displacement of the tension suture material alters the circumferential position of the protection device in relation to the underlying coronary arteries. This embodiment allows the protection device to be positioned over the protected coronary artery by longitudinal displacement of the tension suture material.

The protection device can be incorporated, by modification, into a coronary sinus shortening system already publicly disclosed, tested, or marketed, for the treatment of mitral valve regurgitation.

In another described embodiment of a transcatheter coronary sinus procedure, annuloplasty is performed by advancing a wire through the catheter into the coronary sinus to a coronary vein branch such as an anterolateral cardiac vein, and then across myocardial or fibrous tissue of the heart through the left ventricular chamber, and further across myocardium into the right ventricular or right atrial cavity. The wire is then exchanged to introduce tensioning material through the coronary sinus, and tension is applied on the tensioning material to alter the shape of the heart or valves and reduce unwanted, for example deleterious, cardiac remodeling or valvular regurgitation.

Different lengths of protection devices may be made available to offer protection for narrow or wide segments of single or multiple coronary arteries potentially compressed by the cerclage or other annuloplasty device. Similarly, multiple protection devices may be used in tandem to offer protection to adjacent or nonadjacent circumferential segments potentially compressed by the cerclage or other annuloplasty device. Similarly the protection devices can be employed to protect other cardiac structures that may be compromised by the annuloplasty tension element, such as from focal erosion of the myocardium or laceration of the tricuspid valve leaflet.

BRIEF DESCRIPTION OF THE FIGURES

FIGS. 1A and 1B show two embodiments of the protective device. FIG. 1A is a side elevational view of a first embodiment of the protective device which has a central curved arch and two substantially linear end portions that extend in the same plane as one another and function as support feet. The protective device has a hollow lumen through which a ligature (for example, and without limitation, a wire or suture) can pass, as shown by the broken line. FIG. 1B is a side elevational view of another embodiment of the protective device. In this embodiment, the protective device has a central curved portion and no support feet.

FIG. 2 is a schematic view showing the protective device in position during a cerclage annuloplasty procedure. The ligature encircles the mitral annulus via the coronary sinus, and the protective device is positioned over a coronary artery where the coronary sinus lies superficial to the artery.

FIGS. 3A-3D are a set of drawings showing the region of the heart involved in trans-sinus coronary annuloplasty and illustrating the use of the protective device to prevent pinching of the coronary artery when tension is applied to a cerclage tensioning device. FIG. 3A is a left lateral external perspective view of the heart showing the lateral coronary artery branching from the ascending aorta, the branch of the lateral circumflex artery, and the great cardiac vein. FIG. 3B is an enlarged view of a section of the arteries showing the coronary sinus crossing superficial to the left circumflex coronary artery at the level of the great cardiac vein. FIG. 3C is a view similar to FIG. 3B but showing placement of a ligature (for example, and without limitation, a wire or suture) during annuloplasty without the protective device in place. When the ligature is tightened during the annuloplasty procedure, pressure is exerted on the branch of the coronary artery, restricting blood flow and myocardial perfusion. FIG. 3D is an enlarged view of this same structure showing placement of the protective device over the ligature within the coronary sinus and superficial to the coronary artery.

FIG. 4A is a schematic top view of a human heart, taken at the level of the atrioventricular valves, showing in dashed lines two alternative trajectories of the cerclage annuloplasty ligature around the mitral valve.

FIG. 4B is a front perspective view of the heart with portions of the myocardial wall broken away to show the cerclage annuloplasty trajectories of FIG. 4A.

FIG. 4C is a rear perspective view of the heart showing the tilted plane of the coronary sinus cerclage annuloplasty. The drawing schematically illustrates a smaller traditional surgical mitral valve annuloplasty ring over the mitral valve annular plane and the larger coronary artery cerclage in a plane that is tilted to the mitral plane so as to encompass the left ventricular outflow tract.

FIG. 5 is a side elevational view of one embodiment of the protective device for protecting a coronary artery from compression during the annuloplasty procedure, showing a device made of nitinol with a surgical suture (black monofilament nylon) ligature extending through the device.

FIG. 6 is a digital image of a left coronary angiogram before tension is applied to a mitral annuloplasty wire in a pig. Arrows indicate the position of the annuloplasty wire that encircles the mitral annulus via the coronary sinus.

FIG. 7 is a digital image of a left coronary angiogram showing a part of the left circumflex artery that is severely pinched by an annuloplasty wire that encircles the mitral annulus via the coronary sinus in a pig.

FIG. 8 is a digital image of a left coronary angiogram showing that the protective device protects the coronary artery from compression when tension is applied to a wire ligature that encircles the mitral annulus via the coronary sinus in a pig.

FIG. 9 is a series of four digital images of angiograms showing that the severity of compression of the left circumflex artery was positively correlated with the magnitude of tension applied to the cerclage ligature (without the protective device).

FIGS. 10A-10D show the results of cerclage annuloplasty without (FIG. 10A, FIG. 10C) and with (FIG. 10B, FIG. 10D) the protective device. FIGS. 10A and 10B are digital images of coronary angiograms, while FIGS. 10C and 10D are intracoronary pressure recordings.

FIG. 11 is a schematic cross-sectional view of the mitral valve region of a heart wherein a prosthetic heart valve is positioned within the mitral valve region and applies an outward expansion force and a mitral cerclage device is positioned around the mitral valve region and applies an inward force, and a protection device is positioned along the mitral cerclage device to protect the coronary artery from being compressed.

FIG. 12 is a cross-sectional view of a heart with a mitral cerclage device being delivered through the coronary sinus and around the mitral valve.

FIG. 13 is a cross-sectional view of a heart with a prosthetic mitral valve mounted within the native mitral valve region and a mitral cerclage device positioned through the coronary sinus and around the mitral valve region with a protection device protecting the coronary artery from compression.

FIGS. 14 and 15 are schematic diagrams illustrating the relative positions of feet of a protective member relative to the curvature of the heart tissue.

FIG. 16 illustrates an oblique crossing angle as the mitral cerclage device and protection member pass over the coronary artery.

FIG. 17 illustrates an exemplary protection device having a chiral shape that allows it to cross at an angle perpendicular to the coronary artery.

FIG. 18 shows another exemplary protection device having a chiral shape that includes a three-dimensional curvature.

DETAILED DESCRIPTION OF SEVERAL EMBODIMENTS

I. Explanation of Terms

Unless otherwise noted, technical terms are used according to conventional usage. In order to facilitate review of the various embodiments of the disclosure, the following explanation of terms is provided:

“Annuloplasty element” refers to a device that induces reshaping of an annulus of the heart to repair valvular insufficiency. Such devices include those that are placed in the coronary sinus and exert their action by compressive forces on the annulus, for example by expansion of a resilient annuloplasty element, or placement of the annuloplasty element under tension, as in cerclage annuloplasty.

The term “comprises” means “includes without limitation.” Thus, “comprising a guiding catheter and a guide wire” means “including a guiding catheter and a guide wire,” without excluding additional elements.

The term “guide wire” refers to a simple guide wire, a stiffened guide wire, or a steerable guide-wire catheter that is capable of puncturing and/or penetrating tissue. The guide-wire also can deliver energy to augment its ability to penetrate tissue, for example by puncturing it, delivering radiofrequency ablative energy or by delivering laser ablative energy. These are examples of a “penetrating device,” which is a device capable of penetrating heart tissue, such as the myocardium.

As used herein, the term “ligature” is meant to encompass any suitable tensioning material and is not limited to only suture material. The term “tensioning material” or “ligature” includes sutures and annuloplasty wires.

A “mitral valve cerclage annuloplasty” refers to an annuloplasty procedure in which a tensioning element is placed through at least a portion (and preferably all) of the coronary sinus so that the circumferential tension is delivered around the mitral valve annulus and so that a tensioning element can be placed under selective degrees of tension to perform the annuloplasty. An example of cerclage annuloplasty is disclosed in co-pending prior application 11/127,112 (U.S. Patent Publication No. 2005/0216039), and the disclosure of the description of that technique is incorporated herein by reference. However, the mitral valve cerclage annuloplasty technique also includes other cerclage trajectories, such as those disclosed herein, including a trajectory through a proximal coronary septal perforator vein and myocardium or annulus fibrosis interposing between that vein and the right ventricle or right atrium to create circumferential cerclage annuloplasty tension.

The protective (or protection) device disclosed herein can be made of an “MRI-compatible” material. Such materials are safe to use in the body during magnetic resonance imaging of the body, and do not substantially affect imaging quality of the MRI. An “MRI-safe” material is one that does not add substantial risk to a human or equipment by placing it in the magnetic field of an MR environment. Examples of MRI-compatible materials are non-ferrous materials, such as ceramics, plastics and non-magnetic composite materials. Austenitic stainless steels (of the 300 series) are neither ferromagnetic nor paramagnetic and therefore are MRI-compatible. Titanium and aluminum are MRI-compatible, even though they are not ideally paramagnetic. Particularly disclosed MRI-compatible materials of which the protective device may be made include nitinol, MP35N and cobalt-chromium alloys.

“Tensioning material” is any material suitable to perform a coronary sinus mitral valve cerclage annuloplasty, in which an encircling material is placed under tension to remodel the mitral valve annulus. Examples of suitable tensioning materials are the ligature materials already described.

Unless otherwise explained, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this disclosure belongs. The singular terms “a”, “an”, and “the” include plural referents unless context clearly indicates otherwise. The term “or” refers to a single element of stated alternative elements or a combination of two or more elements, unless context clearly indicates otherwise. For example, the phrase “rtMRI or echocardiography” refers to real-time MRI (rtMRI), echoradiography, or both rtMRI and echocardiography. Although methods and materials similar or equivalent to those described herein can be used in the practice or testing of the present disclosure, suitable methods and materials are described below. In case of conflict, the present specification, including terms, will control. In addition, the materials, methods, and examples are illustrative only and not intended to be limiting.

II. Protection Devices to Protect Coronary Arteries During Mitral Valve Cerclage Annuloplasty

Coronary sinus mitral valve cerclage annuloplasty is an example of a percutaneous mitral valve repair procedure for which the disclosed protective device can be used. Although the device and methods of its use are broadly applicable to any prosthetic annuloplasty element placed in the coronary sinus, the methods will be described in connection with the particular example of cerclage annuloplasty. This specific example should not be construed to limit the procedure to use with cercalge annuloplasty, but only to illustrate its use in a particular embodiment.

Cerclage annuloplasty percutaneous repair carries a lower risk or morbidity than conventional mitral valve surgery, and thus can be used in patients who have less severe or more severe valvular dysfunction. Placing cerclage ligatures at least partially through the coronary sinus takes advantage of the proximity of the coronary sinus to the mitral valve annulus, and of the ready catheter access to the coronary sinus and tributary veins. These approaches also have limiting drawbacks, however, in that compression of nearby coronary artery branches is a serious risk in a majority of human subjects. The coronary sinus usually runs superficial to the circumflex coronary artery and its marginal branches near the great cardiac vein, and therefore trans-sinus annuloplasty can transmit pressure sufficient to constrict or occlude the coronary artery or its branches. Devices and methods that prevent this compression of the coronary artery, such as those disclosed herein, can dramatically increase the safety and efficacy of trans-sinus mitral cerclage annuloplasty.

An exemplary transcatheter-mitral-valve-cerclage annuloplasty involves the introduction of a tensioning material or device around the mitral valve annulus using a guiding catheter and a secondary catheter, such as a steerable microcatheter directing coaxial guide wires or canalization catheter. Access to the area around the mitral-valve annulus can be accomplished using a variety of percutaneous approaches, including access from and through the coronary sinus. In particular embodiments, a continuous strand of tensioning material also referred to as a cerclage ligature (for example, and without limitation, a tensioning material such as a wire or suture) is applied around the mitral-valve annulus along a pathway that, in certain embodiments, includes an extra-anatomic portion. For example (and without limitation), the tensioning material can traverse a region between the anterobasal-most portion of the coronary sinus and the coronary-sinus ostium. As another non-limiting example, tensioning material can be applied across the atrial aspect of the mitral valve from the posterolateral aspect to the anterior aspect of the coronary sinus, or from the septal aspect to the lateral aspect of the mitral-valve annulus. This procedure reduces the mitral annular cross-sectional area and septal-lateral wall separation, thereby restoring a line of coaptation of the mitral valve.

Because it has now been found that mitral annuloplasty via the coronary sinus unintentionally transmits pressure sufficient to constrict or occlude the underlying coronary artery, the devices disclosed herein have been developed to increase the safety and efficacy of the procedure. The disclosed devices protect an underlying vessel from compression during mitral annuloplasty in which a cerclage ligature extends at least partially through the coronary sinus over a coronary artery. In one embodiment shown in FIG. 1A, the device is a surgically sterile protection device or bridge 20 of a suitable shape and size to permit its introduction through a transvascular catheter into the coronary sinus. The protection device has an internal lumen extending its length through which a mitral cerclage tension element 22 can extend and be placed under tension, and the protection device also includes a central arch 24 of sufficient rigidity and dimensions to inhibit application of pressure to the underlying left circumflex artery when the cerclage tension element is placed under tension during mitral valve annuloplasty. For example, the protection device has a semi-circular shape of sufficient radius to extend closely over an underlying coronary artery to inhibit the transmission of compressive forces from the tension element to the underlying artery. The compressive forces are instead distributed on and along the protection device to protect the artery from compression that impairs myocardial perfusion.

In the embodiment of FIG. 1A, the central arch of the device extends between a proximal end portion 26 and a distal end portion 28 of the protection device, and the proximal and distal end portions are not curved but extend in substantially the same plane as one another, radially away from the arch, to form stabilizing feet 30, 32 that can rest against a wall of the coronary sinus while straddling a coronary artery to retain protection device 20 in position over the left circumflex artery and bear and distribute the compressive forces that are applied by ligature 22 under tension. The example of the device illustrated in FIG. 1A has a central arch bridging a linear distance d1 at its base of from about 0.5 inches to about 0.6 inches, for instance, from about 0.52 inches to about 0.55 inches, or about 0.536 inches. The illustrated central arch has a height h from about 0.15 inches to about 0.16 inches high, for instance, about 0.1545 inches high. These dimensions are examples of dimensions that can be assumed by the device, which help it conform closely to without occluding a coronary artery.

The illustrated embodiment of the protection device in FIG. 1A is a generally tubular member having an outer diameter from about 0.04 to about 0.05 inches, and the inner diameter is from about 0.025 inches to about 0.035 inches along its entire length. In particular examples, the protection device outer diameter is about 0.045 inches along its entire length, and in other particular examples, the diameter of the inner lumen is from about 0.025 inches to about 0.035 inches along its entire length, for instance, about 0.030 inches along its entire length. In even more particular examples, the central arch bridges a linear distance at its base about 0.536 inches, the central arch is about 0.1545 inches high, the protection device outer diameter is about 0.045 inches, and the inner diameter is about 0.030 inches. In certain examples, the device is made from a shape memory material, for instance a nickel titanium alloy such as nitinol, that allows the device to be deformed (for example toward a linear configuration) that is adaptable to introduction through the vascular system. However, the shape memory material returns to the arched configuration shown in the drawings after the device is deployed from a delivery catheter.

FIG. 2 schematically illustrates the use of protection device 20 in a mitral valve cerclage annuloplasty procedure. FIG. 2 depicts tensioning element 22 (suture material) extending through a portion of the coronary sinus 50 over a circumflex coronary artery 52. FIG. 2 shows protection device 22 is positioned within coronary sinus 50 with arch 24 extending over coronary artery 52, and feet 30, 32 on either side of coronary artery 52. As tension is placed on tensioning element 22 the support feet 30, 32 are held in place on either side of coronary artery 52 and transmit compressive forces to the wall of coronary sinus 50 instead of on to underlying coronary artery 52.

FIGS. 3A, 3B, 3C and 3D provide an alternative view of the function of cerclage annuloplasty protection device 20. FIG. 3A shows the external anatomy of the heart, with coronary sinus 50 extending over a circumflex branch 52 of a left coronary artery 54. FIG. 3B shows an enlarged view of the overlapping relationship of coronary sinus 50 to coronary artery 52. FIG. 3C illustrates tension element 22 placed under tension during cerclage annuloplasty which is compressing underlying coronary artery 52 and interfering with myocardial perfusion. FIG. 3D shows tensioning material 22 extending through protection device 20 which is inhibiting the application of compressive force to coronary artery 52 which therefore remains patent and able to normally perfuse myocardial tissue.

An alternative embodiment of the protection device is shown in FIG. 1B, in which a protection device 54 is tubular so that an internal lumen extends through it to accommodate tension material 22. However this embodiment is shaped into a generally arcuate (for example parabolic or catenary shape instead of semi-circular) arch 56. The distance d2 spanned by arch 58 is slightly greater than the distance d1 spanned by arch 24 in the embodiment 20 of FIG. 1A because of the more gradual slope of arch 44. Protection device 54 of FIG. 1B also does not have the support feet of the embodiment 20 shown in FIG. 1A, and compressive forces are distributed directly from proximal and distal feet 58, 59 of protection device 50 to a wall of the coronary sinus at a position other than over an underlying coronary artery.

The protection device can assume a variety of shapes and configurations that support the tensioning material away from an underlying coronary artery. The protection device can be pre-shaped to the desired configuration, or it can be made of a memory alloy material that is generally linear when being advanced through the guidance catheter but assumes the desired protection device shape once it is deployed from the guidance catheter over the tensioning material.

Although the illustrated protection devices are tubular, a tubular structure is not necessary. For example, the protective device can take the form of a support or bridge having an open top on which the tensioning material is supported. The support would preferably have side guides (such as curved or upright members) that help retain the tensioning material on the support by resisting lateral forces that could dislodge the tensioning material from the support, while permitting longitudinal movement of the tensioning material along the support.

III. Percutaneous Mitral Valve Cerclage Annuloplasty

A. Mitral Regurgitation

Regurgitation (leakage) of the mitral valve or tricuspid valve can result from many different causes, such as ischemic heart disease, myocardial infarction, acquired or inherited cardiomyopathy, congenital defect, traumatic injury, infectious disease, and various forms of heart disease. Primary heart muscle disease can cause valvular regurgitation through dilation, resulting in expansion of the valvular annulus leading to malcoaptation of the valve leaflets through overstretching, degeneration, or rupture of the papillary muscle apparatus, or through dysfunction or malpositioning of the papillary muscles. This regurgitation can cause heart rhythm abnormalities such as atrial fibrillation, which itself can cause inexorable deterioration in heart muscle function. Such deterioration can be associated with functional impairment, congestive heart failure and significant pain, suffering, lessening of the quality of life, or even premature death.

A less dangerous, minimally invasive procedure, such as percutaneous annuloplasty, permits more patients to undergo mechanical treatment of valvular regurgitation.

B. Percutaneous Cerclage Annuloplasty

Because the risks and complications of surgery are reduced (compared with open-heart surgery), catheter-based heart-valve procedures are suitable for a broader population of patients. Disclosed herein are devices and methods for catheter-based valve repair that can be used to repair damaged or malfunctioning cardiac valves, for instance, by re-apposing valve leaflets by percutaneous-cerclage annuloplasty (reconstruction or augmentation of the ring or annulus of a defective cardiac valve). In some instances, percutaneous cerclage annuloplasty is used to deliver circumferential or radial tensioning devices. Examples of some of these procedures are described in detail in WO2004/045378 and US 2005/0216039, which are incorporated herein by reference.

In general, the system used to carry out an annuloplasty procedure can include a guiding catheter (GC), such as a preformed transjugular balloon-tipped guiding catheter which is introduced into the coronary (venous) sinus. A retrograde coronary radiocontrast venogram pressurizes and visualizes the great cardiac vein and septal perforator veins. A high performance guidewire designed for coronary artery recanalization may be steered using a deflectable microcatheter into the great cardiac vein and thereafter into a basal septal perforator vein.

In general, an annuloplasty procedure also can include using an imaging system to image the internal bodily tissues, organs, structures, cavities, and spaces of the subject being treated. For example, transmitter or receiver coils can be used to facilitate active-device navigation using an imaging system, such as magnetic-resonance imaging (MRI). This imaging can be conducted along arbitrary or predetermined planes using various imaging methods based on X-ray technologies, X-ray fluoroscopy, MRI, electromagnetic-positron navigation, video technologies (such as endoscopy, arthroscopy, and the like), ultrasound, and other such technologies. In some embodiments, real-time MRI (rtMRI), intracardiac ultrasound, or electromagnetic guidance is employed. A particularly useful adjunct in cerclage annuloplasty is XFM, in which X-Ray is used with MRI to target myocardial structures, for example to help guide the annuloplasty wire in its trajectory through the structures of the heart. The XFM technique is disclosed, for example, in de Silva et al., Circulation 114:2342-2350 (2006).

The guiding catheter enables percutaneous access into a subject's body, for example, percutaneous access to the heart, such as a chamber of the heart through an arm, neck, or leg vein. In some embodiments, the guiding catheter is designed for access to the ventricle and/or atrium of the heart. The guiding catheter permits introduction of one or more secondary catheters, including a valve-manipulation catheter or microcatheter or canalization-needle catheter. The secondary catheter (or catheters) is used to treat, affect, or manipulate an organ, tissue, or structure of interest in the subject's body, such as the heart or particular structures within the heart. If the guiding catheter is used for percutaneous (or other) access to the heart, the guiding catheter permits introduction of one or more secondary catheters, such as a valve-manipulation catheter, into the heart while maintaining hemostasis. The secondary catheters may be coaxial or adjacent to each other, or may be introduced from multiple points of access outside the body.

Guiding catheters are available in different shapes to suit the appropriate component of the mitral-valve-repair procedure. For example, guiding catheter shapes can be provided to suit different coronary sinuses with different radii of curvature, to suit different coronary veins, transaortic as well as transseptal access routes, or to suit atria and ventricles of different calibers. All such shapes can be accommodated with appropriate primary, secondary, and tertiary curves. Examples of catheter configurations suitable to perform percutaneous transvascular mitral valve annuloplasty are know in the art and described in detail in U.S. Patent Publication No. 2005/0216039, which description is incorporated by reference herein.

Although any available approach to the coronary sinus may be used, a venous approach is preferred, for example through the jugular vein. As yet another example, the guiding catheter can be introduced into a vein, such as the femoral or jugular vein, and guided through the inferior or superior vena cava into the right ventricle of the heart.

Two examples of trajectories for cerclage annuloplasty are shown in FIG. 4A and FIG. 4B. The first trajectory (labeled a “simple” or “RV” trajectory) is one in which the annuloplasty wire enters the right atrium through the superior vena cava and is then introduced through the coronary ostium into the coronary sinus. The wire is advanced through the great cardiac vein into a basal blood vessel, such as a basal septal perforator vein. The wire then exits the septal perforator vein through myocardial interstitium into the right ventricle, re-entering the right atrium along the septal tricuspid valve commisure (at the intersection of the anterior cusp and the septal cusp). The guidewire is then retrieved using, for example, a vascular snare, and the guiding catheter and guidewire are replaced with a different tensioning system, such as a tensioning suture. The replacement can occur, for example, by attaching the tensioning material to the guidewire and advancing the tensioning material along the path of the guidewire as the guidewire is withdrawn. The protection device is then introduced through the guiding catheter over or in tandem with the tensioning system so as to protect an underlying coronary artery when tension is introduced to perform the annuloplasty. The location of the jeopardized coronary artery is identified, for example, by radiocontrast angiography. In an alternative approach, coronary veins are entered in the opposite direction from the right atrium or right ventricle under imaging guidance into a branch of the coronary sinus.

An alternative or “complex” right atrial cerclage trajectory shown in FIGS. 4A and 4B extends further posterior through the basal septal myocardium into the right atrium near the coronary sinus. The wire traverses deep tissue of the septum moving in a posterior direction and exits above the opening of the coronary sinus.

The plane of the resulting cerclage annuloplasty is shown in FIG. 4C to be related to and in the plane of the coronary sinus 60 such that annuloplasty remains uniquely feasible even if the coronary sinus is remote from the mitral valve annuloplasty. As the figure indicates, the plane of cerclage 60 enhances mitral valve coaptation, even when the coronary sinus is geometrically remote from the mitral valve annulus, because it is “tilted” toward the left ventricular outflow tract. The illustrated angle α between the cerclage plane 60 and the plane of the mitral valve annulus 62 is therefore advantageous. Moreover, the illustrated trajectories of the cerclage annuloplasty induces reciprocal mitral valve coaptation and left ventricular outflow tract relaxation during ventricular systole.

The guide wire is dimensioned to operate with the catheter and is usually longer than the guiding catheter. For example, a guide wire of about 100 to about 250 centimeters in length and about 0.1 to about 2 mm in diameter can be used with the guiding catheter described above. If a secondary catheter, such as a tension delivery catheter, is intended for use with the guiding catheter, that secondary catheter also is dimensioned to operate with the guiding catheter and is usually longer than the guiding catheter.

The guiding catheter can be made of any suitable material or combination of materials that provide both the strength and flexibility suitable to resist collapse by external forces, such as forces imposed during bending or twisting. Exemplary materials include, but are not limited to: polymers, such as polyethylene or polyurethane; carbon fiber; ceramic; or metals, such as nitinol, platinum, titanium, tantalum, tungsten, stainless steel, copper, gold, cobalt-chromium alloy, or nickel. The guiding catheter optionally can be composed of or reinforced with fibers of metal, carbon fiber, glass, fiberglass, a rigid polymer, or other high-strength material. In particular embodiments, the guiding catheter material is compatible with MRI, for example, braided nitinol, platinum, tungsten, gold, or carbon fiber. Additionally, the exterior surfaces of the guiding catheter can be coated with a material or substance, such as Teflon® or other lubricous material that aids with the insertion of the guiding catheter into the body of the subject and/or aids in the movement of the guiding catheter through the subject's body.

Additionally, the guiding catheter can include a deflectable tip, such as a simple deflectable tip having a single degree of axial freedom. Exemplary (non-limiting) fixed-fulcrum and moveable-fulcrum-deflectable-tip catheters are commercially available, such as the deflectable-tip catheters described in U.S. Pat. Nos. 5,397,321; 5,487,757; 5,944,689; 5,928,191; 6,074,351; 6,198,974; and 6,346,099. Thus, any suitable fixed-fulcrum or moveable-fulcrum deflectable-tip catheter can be adapted for use as a guiding catheter disclosed herein. The guiding catheter also can include structures or mechanisms for aiding in the rotation of the catheter about its longitudinal axis.

The guiding catheter can include a guide collar, handgrip, handle, and other structures or devices at its proximal end that aid in operation of the guiding catheter. Various control mechanisms, including electrical, optical, or mechanical control mechanisms, can be attached to the catheter via a guide collar. For example, a guide wire can be included as a mechanical control mechanism. The guide collar can include additional operational features, such as a grip for aiding manual control of the guiding catheter, markers indicating the orientation of the guiding catheter lumen or subdivided lumens, markers to gauge the depth of guiding catheter advancement, instruments to measure guiding catheter operation or physiological signs of the subject (for example, a temperature gauge or pressure monitor), or an injector control mechanism coupled to the guiding catheter lumen for delivering a small, precise volume of injectate. In some embodiments, the guide collar contains instrumentation electrically coupled to metallic braiding within the guiding catheter, thus allowing the guiding catheter to simultaneously be used as a receiver coil for MRI.

A guide wire used with the system for guiding the guiding catheter into and through a subject's body can be composed of any suitable material, or combination of materials, including the materials described above in relation to the guiding catheter. Exemplary (non-limiting) guide wires are composed of material having the strength and flexibility suitable for use with the device, such as a strand of metal (for example, surgical stainless steel, nitinol, platinum, titanium, tungsten, copper, or nickel), carbon fiber, or a polymer, such as braided nylon. Particular (non-limiting) guide wires are composed of a strand of Nitinol or other flexible, kink-resistant material.

The guiding catheter or guide wire can include an image-enhancing feature, structure, material, or apparatus, such as a radiopaque marker (for example, a platinum or tantalum band around the circumference of the guide wire) adjacent its distal end. As another example, the guide wire can include etchings or notches, or be coated with a sonoreflective material to enhance images obtained via intravascular, intracardiac, transesophogeal, or other ultrasound-imaging method. As another example, the guide wire can be coated with a T1-shortening or T2*-shortening agent to facilitate passive visualization using MRI. As yet another example, a fiber-optic secondary catheter can be inserted into and through a secondary-catheter lumen of the guiding catheter to assist in visualizing the position of the guide wire within the subject as a guide wire is deployed through the distal guide-wire lumen port.

In some embodiments, the guide wire and/or guiding catheter includes a structure, apparatus, or device at its distal tip useful for penetrating tissue, such as myocardial skeleton, muscle, or connective tissue. For example, the distal tip of the guide wire can be sharpened to a point for puncturing through tissue, or a secondary catheter having a coring mechanism or forceps at its distal tip can be used in conjunction with the guiding catheter. In alternative embodiments, the guide wire can deliver radiofrequency or laser ablative energy to assist with traversal of tissue. However, in alternative embodiments, the distal end of the guide wire is bent to provide a J-shaped or a pigtail-shaped tip to protect against perforation of tissue by the guide wire during manipulation. In still other alternative embodiments, the guide wire itself has a deflectable tip to facilitate traversal of tissue irrespective of natural tissue planes.

One or more secondary catheters can be deployed within the lumen of the guiding catheter. Like the guiding catheter, each secondary catheter has a proximal end and a distal end; however, not all secondary catheters have a lumen. For example, non-lumen secondary catheters can include various probes, such as temperature probes, radiofrequency or cryogenic ablation probes, or solid needles. An exemplary non-limiting secondary catheter is a canalization needle catheter, which can be deployed through the guiding catheter and into a chamber of the heart to place cerclage annuloplasty ligature through the coronary sinus around the mitral valve. A canalization-needle catheter is a type of secondary catheter that can be used to apply a suture to a bodily tissue, organ, or structure of interest.

Ligatures used for the sutures described herein can be composed of any suitable material, such as surgical cotton, cotton tape, linen, or other natural fiber; nylon, polyester, or other polymer; metal, such as surgical stainless steel or nitinol; carbon fiber; or surgical gut. Ligature materials can be used in a woven, braided, or monofilament form. Suitable ligature and suture materials are commercially available from Ethicon, Inc. (Somerville, N.J.) and other companies.

C. Application of Tension

Tension is applied via the annuloplasty cerclage through, for example, suture material exchanged for the cerclage guidewire. Tension can be applied through both ends of the suture as they are externalized at the point of vascular access. Tension is applied under imaging guidance until the desired degree of mitral annular circumferential reduction is accomplished, or until the mitral valve regurgitation is reduced, or until other deleterious endpoints are achieved such as mitral valve inflow obstruction. Tension is secured using a knot or using a tension fixation device applied to both ends of the suture at the right atrium or right ventricle where the two cerclage trajectories cross, or at the point of vascular access, or in between the two. Tension is delivered by counterpressure against the fixation device, for example, applied through a delivery catheter. Before fixation, tension can be released or reduced, for example, to reposition the protection device or to achieve a lower degree of mitral annular circumferential reduction.

As tension is applied, valvular regurgitation is assessed repeatedly and non-invasively by an appropriate imaging technique. Such imaging techniques include X-ray angiography, electromagnetic position detection, MRI, external or intracavitary or intravascular ultrasound, X-ray computed tomography, pressure transducers in an affected chamber such as the left atrium or the pulmonary vein or the pulmonary artery, or a “fusion” or combination of any of the above. After the valvular regurgitation has been reduced (or even eliminated) and a desired tension is achieved, the tension is fixed using a knot delivery system. If the resulting circumferential suture is knotted to form a closed loop, the suture essentially becomes a cerclage suture.

Without further elaboration, it is believed that one skilled in the art can, using this description, utilize the present discoveries to their fullest extent. The following examples are illustrative only, and not limiting of the disclosure in any way whatsoever.

Example 1: Annuloplasty Using Protective Device with Percutaneous Transluminal Coronary Angioplasty Wire for Cerclage

This Example demonstrates the efficacy of one embodiment of the protective device in protecting the coronary artery from compression during trans-sinus annuloplasty. In this Example, the protective device was constructed of a stainless-steel hypotube (FIG. 5). A 57 kg Yucatan pig was anesthetized, and after obtaining vascular access in the right jugular vein, the femoral vein, and the femoral artery, an annuloplasty wire (0.014 conventional percutaneous transluminal coronary angioplasty (PTCA) wire) was positioned around the mitral annulus to form a cerclage using the method described herein in which tensioning material passes through the coronary sinus over a coronary artery. FIG. 6 shows the left coronary angiogram of the subject with the wire in position, but before tension was applied.

After encircling the mitral annulus with the annuloplasty wire via the coronary sinus, tension was applied by traction on both ends of the externalized guide wire. When tension was applied to the wire, a focal segment of left circumflex artery was constricted where the coronary sinus lies superficial to the artery, so that the minimal lumen diameter of left circumflex artery decreased from 2.0 mm to 0.3 mm (FIG. 7).

By contrast, when this same protocol was carried out a second time, but the protective device was positioned over the left circumflex artery branch, the coronary constriction was reduced to 1.5 mm of minimal luminal diameter of left circumflex artery when the same tension was applied to the wire (FIG. 8). Thus, the protective device protected the coronary artery from extrinsic compression during trans-sinus annuloplasty.

Example 2: Annuloplasty Using an Alternate Embodiment of the Protective Device

To quantify the protective ability of the device, the pressure in the left circumflex artery was measured using a conventional coronary pressure wire (Radi pressure wire). A 65 kg Yucatan pig was anesthetized, and after obtaining vascular access in the right jugular vein, the femoral vein, and the femoral artery, an annuloplasty wire (0.014 conventional PTCA wire) was positioned around the mitral annulus to form a cerclage essentially as described in Example 1. After placing the cerclage, but before tension was applied, the pressure wire was positioned at a site in the left circumflex artery that was distal to the point where the cerclage passed over the coronary artery. Distal coronary pressure was measured while tension was applied with and without the protective device in place over the left circumflex artery branch. The protective device ameliorated the reduction in distal coronary artery pressure caused by the tension in the cerclage.

Example 3: Annuloplasty Using a Third Embodiment of the Protective Device

This Example demonstrates the efficacy of another alternate embodiment of the protective device. For this Example, the protective device was modified to augment the height of the central curve, and thereby further protect the coronary artery from compression during annuloplasty. A 74 kg Yucatan pig was anesthetized, and after obtaining vascular access in the right jugular vein, the femoral vein, and the femoral artery, an annuloplasty wire (0.014 conventional PTCA wire) was positioned around the mitral annulus to form a cerclage essentially as described in Example 1. After placing the cerclage, the end of cerclage wire from the right jugular vein was fixed and graded tensions of 0 grams, 200 grams, 400 grams and 600 grams were applied through the femoral end of a cerclage wire with and without the protective device in position over the left circumflex artery branch. FIG. 9 is a series of angiograms that show the effect on blood flow through the left circumflex artery when mild, moderate, and maximal tension was applied to the wire without the protective device in position.

The protective device was then positioned over the left circumflex artery branch and the same tensions were applied to the cerclage wire. While the phenomenon of coronary pinching became more pronounced as the tension increased, use of the protective device completely abated the drop in blood pressure that was observed when the protective device was not used (FIGS. 10A-10D). The augmented height of the curve of the protective device in this embodiment improved the angiographic protection effect as compared to the protective devices of Examples 1 and 2.

Example 4: Use of the Protection Device with a Suture Cerclage

This Example demonstrates the efficacy of the protective device when used with a suture cerclage instead of a PTCA wire. A biocompatible suture material is a suitable cerclage ligature in many applications, however the metallic PTCA wire used in Examples 1-3 has different properties than a biocompatible suture. To determine whether the flexibility of the suture material affects the function of the protective device, the device was tested during a suture-based cerclage annuloplasty. A 55 kg Yorkshire pig was anesthetized, and after obtaining vascular access in the right jugular vein, the femoral vein, and the femoral artery, an annuloplasty wire (0.014 conventional PTCA wire) was positioned around the mitral annulus to form a cerclage essentially as described in Example 1. This procedure was then repeating using a conventional surgical suture that was made of non-absorbable black mono nylon with a thickness of 0.014 inches.

For this Example, the dimensions of the protective device were altered and the device was made from nitinol which is MRI-compatible. The width and height of the device were 0.536″ and 0.1545″ respectively, and the diameter of inner lumen and outer surface were 0.030″ and 0.045″ respectively. Tension was applied using the same method described in Examples 1-3. When tension was applied, a focal segment of proximal left circumflex artery was completely obstructed.

The protective device was positioned over the left circumflex artery branch via delivering catheter and tension was applied as described above. This embodiment of the protective device afforded complete protection (no coronary compression) at comparable annuloplasty cerclage tensions. Thus, this embodiment of the protection device completely prevents coronary artery compression when used in combination with a suture cerclage.

Example 5: Use of the Protection Device with Other Coronary Sinus Annuloplasty Techniques

The use of the protective device has been disclosed for use in a cerclage annuloplasty technique. However, the protective device can be used with any other annuloplasty device that extends even partially through the coronary sinus in a region that crosses an underlying coronary artery. For example, the protective device can be used to protect against compression of coronary arteries with any coronary sinus annuloplasty device, such as the coronary sinus device in U.S. Pat. No. 7,090,695 or the inflatable coronary sinus device shown in U.S. Ser. No. 10/787,574 (U.S. Patent Publication No. 2004/0254600). Although these devices are designed for endovascular delivery, the protection device disclosed herein can also be used with annuloplasty devices that are implanted using an open-chest surgical repair instead of a catheter based approach. The problem of coronary artery compression is also encountered with these devices, and the protective device disclosed herein may be used to avoid that problem. Hence the invention disclosed herein is not limited to a protective device for use with cerclage annuloplasty, nor is it limited to use of the device with catheter based delivery techniques.

When used with a coronary sinus annuloplasty implant of any kind, the protective device can be provided as an integral part of the implant or as a separate device suitable for placement between the implant and an underlying coronary artery to be protected. When provided as an integral part of the implant, the implant is positioned in the coronary sinus so that the arch of the support extends over the underlying coronary artery. In alternative embodiments the protection device is provided as a separate device that is advanced through the catheter system over the tensioning material until it is positioned over the coronary artery to be protected.

IV. Protection Devices Used with Transcatheter Mitral Valve Implant

A mitral cerclage annuloplasty device, as described herein, can push heart tissue radially inwardly and create a retaining structure projecting into the heart near the native mitral valve region to allow implantation and securement of a prosthetic transcatheter mitral valve (TMV). As used herein, the terms prosthetic mitral valve, transcatheter mitral valve, TMV, prosthetic mitral device, prosthetic mitral implant, and the like, include any prosthetic device implantable within or adjacent to the native mitral valve region, including valved devices and as well as devices that do not include a valve component (e.g., frames, stents, rings, fasteners, tethers, portions of a valved device, etc.). In some embodiments, cerclage annuloplasty can create an internal ridge, landing zone, fixation plane, etc. (referred to herein generally as a “retaining structure”) for a TMV to be secured.

The TMV secured to the retaining structure within the heart can comprise a radially compressible and radially expandable prosthetic device that is delivered into the heart in a radially compressed state using a transcatheter, transvascular delivery approach, for example. Once inside the heart, the TMV can expand, either using applied expansion force (e.g., an inflatable balloon) or using intrinsic self-expanding materials (e.g., nitinol) that cause the TMV to self-expand upon removal of a compressive force applied during delivery. Upon expansion, the TMV can become secured to the retaining structure created by the mitral cerclage annuloplasty device to inhibit the TMV from migrating out of position within the heart. For example, the TMV can comprise a tubular frame that expands around both sides of the retaining structure and/or clamps onto the retaining structure.

When expanded, the implanted TMV can apply a radially outward force on the heart tissue. This radially outward force can undesirably compress blood vessels in the heart tissue and cause constriction and reduced blood flow. At the same time, the radially inward force applied by the mitral cerclage annuloplasty device can also undesirably compress blood vessels in the heart tissue from the outside. This dual compression on the cardiac blood vessels can exacerbate the risk of ischemia, heart attack, and other complications. Of particular concern are the circumflex coronary artery and its marginal branches near the great cardiac vein, which can between the implanted TMV and the surrounding mitral cerclage annuloplasty device. Accordingly, disclosed protection devices can help protect such blood vessels from compression from both the outside-in (via the mitral cerclage annuloplasty device) and from inside-out (via the TMV).

FIG. 11 is a schematic cross-sectional view of the mitral valve region of a heart showing an exemplary implant system 100 that includes an implanted TMV 112 positioned within the heart wall 110 and a mitral cerclage annuloplasty device 122 positioned around the heart wall. The device 122 includes an arched protection device 120 spanning over a coronary artery 152 to protect the artery from compression applied by both the device 122 from the outside and outward expansion force 114 applied on the inside of the heart wall 110 by the TMV 112. The exemplary protection device 120 includes an arched portion 124 extending between two feet 130, 132 having respective ends 126, 128. The device 120 can be tubular or non-tubular or partially tubular, can include a groove or slot along all or a portion of its length, and/or can have any combination of features and dimensions described herein with regard to other exemplary protection devices.

FIG. 12 shows a tensioning suture extending through the coronary sinus 150 partially around the mitral valve without the inclusion of the disclosed protection device. Consequently, the circumflex coronary artery 152 is entrapped under the tensioning suture as the coronary sinus overlaps the artery, applying unwanted compression on the artery. When a TMV is also implanted within the mitral valve, it can apply additional inside-out compression force on the artery 152. Without the protection device, the artery 152 can collapse and/or be pinched by the opposing forces.

FIG. 13 shows the approximate locations of the disclosed mitral cerclage annuloplasty device 122 and an exemplary TMV 112 when implanted. As illustrated, the protection device 120 can bridge over the artery 152 (at least partially) and protect it from compression (at least partially) from both the tensioning member on the outside and the TMV on the inside of the heart wall 110. FIG. 13 illustrates the use of a protection member 120 that has an arch portion 124 sized to extend over only about half of the radial thickness of the artery 152, leaving the artery partially exposed to compression. In the illustrated arrangement of FIG. 13, the radially inner half of the artery 152 can be compressed by the opposing forces of the tensioning member and the TMV, leaving the artery partially compressed. In other embodiments, the radially height (e.g., the dimension “h” in FIGS. 1A and 1B) of the arch can be larger (e.g., at least as large as the maximum radial diameter of the artery) to accommodate the most of, or all of, the radially thickness of the artery 152, thereby protecting the artery from compression to a greater degree (e.g., completely or substantially completely) compared to what is shown in FIG. 13. For example, the height “h” can be at least 3.5 mm.

The retaining structure created within the heart by the mitral cerclage annuloplasty device can be oriented in a different plane from an annular or supraannular mitral valve annuloplasty ring or band, whether implanted using surgical techniques or using transcatheter techniques. An example of discordant cerclage and mitral annular planes is illustrated in FIG. 4C. The retaining structure created by the disclosed mitral cerclage annuloplasty can be non-circumferential in part because of the discordant cerclage and annular planes. However, as shown in FIG. 13, the retaining structure can extend around more than half of the full circumference of the mitral valve region so that a TMV can be assured fixation to the retaining structure without undesirable displacement or migration of the TMV.

As discussed, a protection device configured to protect against “inside-out” compression of an entrapped coronary artery can have an increased arch height to more fully protect the artery. However, the increased height can lead to proportionally longer arch length (“d₁” in FIG. 1A) unless the height-to-length ratio is increased. As shown in FIG. 14, this can create an undesired effect where inwardly arched the “elbows” where the arch 120A joins the feet 130A poke into the myocardium and exert a more concentrated compression force right next to the coronary artery rather than having the compression force evenly distributed along the feet 130A.

As shown in FIG. 15, embodiments of the feet 130, 132 of the protection device 120 can include a curvature along the main longitudinal axis of the protection device to allow it to better conform to the curved wall of the heart. This allows a greater height to the coronary artery while avoiding focused compression at the points of contact of the arch elbows along the myocardium immediately alongside the coronary artery. That focused compression limits the protective effect of the arch and may cause undesirable compression or injury or erosium to the myocardium. The curve conformation of the rigid protection member can redistribute the radial force imparted by cerclage tension to better effect protection of the entrapped coronary artery.

Some embodiments of the protection member can have an asymmetric chirality. For example, the protection member can have a helical or corkscrew shape along is longitudinal axis. More generally, the protection member can have a three-dimensional or multi-planar curvature, at least along the arch portion. The asymmetric chirality or multi-planar curvature of the protection member can addresses the problem of the oblique crossing angle of the cerclage tension device with respect to the underlying coronary artery (see FIG. 16). With a symmetrical arched protection member 120 that appears linear when viewed from above the arch (as shown in FIG. 16), the oblique crossing angle reduces the effective width of the arch 124 and reduces its ability to protect the coronary artery 152 against compression. FIG. 17 illustrates an exemplary chiral shaped protection member 120 that curves laterally as it arches over the coronary artery 152 and then curves back the other lateral direction such that the two feet 130, 132 are appear generally parallel but offset when viewed from above the top of the arch (e.g., radially inwardly). This allows the arched portion 124 to cross the coronary artery 152 nearly perpendicularly rather than at an oblique angle as shown in FIG. 16. FIG. 18 shows another exemplary chiral shaped protection device 120 from a partial elevation view, showing an asymmetric chiral shape. The bridge 124 can have a three-dimensional curvature that curved up and over the artery and also curves laterally side-to-side to provide a shorter, more efficient crossing of the artery while keeping the feet 130, 132 oriented along the coronary sinus and facing inward toward the mitral valve.

In view of the many possible embodiments to which the principles of this disclosure may be applied, it should be recognized that the illustrated embodiments are only preferred examples of the disclosure and should not be taken as limiting the scope of the disclosure. We therefore claim all that comes within the scope of the following claims. 

The invention claimed is:
 1. A system comprising: a protection device for protecting a coronary artery of a heart from being compressed between a prosthetic mitral valve secured within a native mitral valve region of the heart and a mitral annuloplasty tension element extending at least partially through a coronary sinus of the heart over the coronary artery; the protection device comprising a protective member comprising a first foot having a first free end, a second foot having a second free end, and an arched portion extending between the first and second feet, the protective member being configured to pass through a transvascular catheter and be implanted within the coronary sinus at a location where the coronary sinus passes over the coronary artery, the protective member being configured to be positioned along an annuloplasty tension element that extends at least partially through the coronary sinus and at least partially around the native mitral valve; wherein the arched portion of the protective member has sufficient rigidity and dimensions to bridge over the coronary artery and inhibit application of compressive pressure on the coronary artery by a prosthetic mitral valve positioned within the native mitral valve region of the heart and exerting an outward expansion force on myocardium underlying the coronary artery while the protective member is positioned in the coronary sinus over the coronary artery and the annuloplasty tension element is under tension; an annuloplasty tensioning element suitable for use with the protection device; and a transcatheter prosthetic mitral valve suitable to be implanted within the native mitral valve region when the annuloplasty tensioning element and the protection device are positioned in the coronary sinus over the coronary artery and applying an inward compressive force on the heart.
 2. The system of claim 1, wherein the annuloplasty tensioning element is configured to create a retaining feature projecting inwardly into the native mitral valve region when extending at least partially through the coronary sinus and placed under tension, wherein the transcatheter prosthetic mitral valve is configured to be secured to the retaining feature by applying radially outward expansion force on the retaining feature, and the protection device is configured to protect the coronary artery from compression by pressure applied by the expansion force of the prosthetic mitral valve.
 3. The system of claim 1, wherein a height of the arched portion is at least 3.5 mm.
 4. The system of claim 1, wherein the arched portion bridges a maximum linear distance of about 0.6 inches.
 5. The system of claim 1 wherein when implanted, tension from the mitral annuloplasty tension element causes the first and second feet of the protection device to orient toward the prosthetic mitral valve when the arched portion is positioned over the coronary artery such that the first and second feet receive the expansion force applied by the prosthetic mitral valve and limit the amount of the expansion force received by the coronary artery.
 6. The system of claim 1, wherein a height of the arched portion is greater than a diameter of the coronary artery such that the coronary artery is protected from compression within the arched portion.
 7. The system of claim 1, wherein the first and second feet of the protection member are curved to match a curvature of the heart wall adjacent to the coronary artery.
 8. The system of claim 1, wherein the protection member has an asymmetric chirality.
 9. The system of claim 1, wherein the protection member has a helical, corkscrew, or spiral shape.
 10. The system of claim 1, wherein the arched portion extends substantially perpendicular to the coronary artery when positioned in the coronary sinus over the coronary artery, while the first and second feet extend at oblique angles relative to the coronary artery.
 11. The system of claim 1, wherein the first foot is offset laterally from the second foot and the arch portion curves laterally along its length as it arches over the coronary artery.
 12. The system of claim 1, wherein the arched portion has a length extending from the first foot to the second foot, the arched portion has a width perpendicular to the length of the arched portion and the height of the arched portion, and the width is substantially uniform along the length.
 13. The system of claim 1, wherein the protection device is at least partially tubular.
 14. The system of claim 1, wherein the protection device is fully tubular.
 15. The system of claim 1, wherein the protection device is non-tubular.
 16. The system of claim 1, wherein the transcatheter prosthetic mitral valve comprises intrinsic self-expanding material that cause the transcatheter prosthetic mitral valve to self-expand within the native mitral valve region upon removal of a compressive force applied during delivery.
 17. The system of claim 16, wherein the transcatheter prosthetic mitral valve is configured to a retaining structure created by inward compression from the annuloplasty tensioning element to inhibit the transcatheter prosthetic mitral valve from migrating out of position within heart after deployment.
 18. The system of claim 1, wherein the transcatheter prosthetic mitral valve is expandable within the native mitral valve region using applied expansion force from.
 19. The system of claim 1, wherein the coronary artery comprises a circumflex coronary artery or a marginal branch of the circumflex coronary artery. 